EP0700309A1 - Electrotransport agent delivery device - Google Patents
Electrotransport agent delivery deviceInfo
- Publication number
- EP0700309A1 EP0700309A1 EP94919291A EP94919291A EP0700309A1 EP 0700309 A1 EP0700309 A1 EP 0700309A1 EP 94919291 A EP94919291 A EP 94919291A EP 94919291 A EP94919291 A EP 94919291A EP 0700309 A1 EP0700309 A1 EP 0700309A1
- Authority
- EP
- European Patent Office
- Prior art keywords
- liner
- components
- mating
- component
- electrotransport
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0428—Specially adapted for iontophoresis, e.g. AC, DC or including drug reservoirs
- A61N1/0448—Drug reservoir
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0428—Specially adapted for iontophoresis, e.g. AC, DC or including drug reservoirs
- A61N1/0432—Anode and cathode
- A61N1/0436—Material of the electrode
Definitions
- This invention relates to electrotransport agent delivery devices, and more particularly, to such devices having reusable and disposable parts.
- Electrotransport refers generally to the passage of a substance through a substrate, such as skin, mucous membrane, or nails, induced by application of an electrical potential.
- a beneficial therapeutic agent may be introduced into the human body by electrotransport.
- electrotransport One type of electrotransport, electroosmosis, involves the movement of a liquid out of or through a synthetic or biological membrane under the influence of an electric field.
- a more widely used electrotransport process, iontophoresis involves the electrically induced transport of charged ions.
- electroporation involves the transport of an agent through transiently-existing pores formed in the substrate under the influence of an electric field. However, in any given electrotransport process, more than one of these processes may be occurring simultaneously to a certain extent.
- electrotransport should be given its broadest possible interpretation so that it includes the electrically induced or enhanced transport of at least one agent, which may be charged, uncharged, or mixtures thereof, regardless of the specific mechanism or mechanisms by which the agent actually is transported.
- Electrotransport devices generally use at least two electrodes which are in electrical contact with some portion of the skin, nails, mucous membrane, or other surface of the body.
- One electrode commonly referred to as the "donor” or “active” electrode, is the electrode from which the agent is delivered into the body.
- the other electrode typically termed the “counter” or “return” electrode, serves to close the electrical circuit through the body.
- an agent to be delivered is positively charged, ie, a cation, then the anode will be the active or donor electrode, while the cathode serves to complete the circuit.
- an agent is negatively charged, ie, an anion
- the cathode will be the donor electrode.
- both the anode and cathode may be considered donor electrodes if both anionic and cationic agent ions are to be delivered.
- electrotransport delivery devices generally require at least one reservoir or source of the agent to be delivered to the body.
- donor reservoirs include a pouch or cavity as described in Jacobsen, US Pat. No. 4,250,878, a porous sponge or pad as disclosed in Jacobsen et al, US Pat. No. 4,141,359, and a pre-formed gel body as described in Webster, US Pat. No. 4,383,529, which are herein incorporated by reference.
- Such donor reservoirs are electrically connected to, and positioned between, the anode or cathode and the body surface, to provide a fixed or renewable source of one or more agents or drugs.
- electrotransport delivery devices have an electrical power source, some having an electrical controller designed to regulate the rate of drug delivery.
- Other optional elements include rate-controlling membranes, insulating members, and protective backing members.
- electrotransport devices may be designed to be distributed in two general components, one being a disposable component and the other being a reusable component.
- the drug or other beneficial agent contained in the donor reservoir may be depleted long before the completion of the useful life of certain hardware used in the device such as the power source or electrical controller.
- the disposable component may contain an agent reservoir and the reusable component may contain an electrical controller component and/or an electrical power source.
- the power source may be a battery having a limited life cycle, while the electrical controller contains long-lasting solid state circuitry.
- the battery may be placed in the disposable component, while the electrical controller is placed in the reusable component.
- a "reusable component” refers to one component of a electrotransport device whose useful life exceeds that of a second component, referred to herein as a "disposable component", wherein the two components may be separated so that the reusable component may subsequently be reused while the disposable component is discarded and replaced with another disposable component.
- the reusable and disposable components are mated to one another, by mechanical and/or electrical connections, in order to form a complete electrotransport device, which device is then adapted to be placed in agent transmitting relation with the body surface (eg, skin or mucosal membrane) of a patient.
- Exemplary of electrotransport delivery devices having reusable and disposable components are those disclosed in US Patent Nos. 4,865,582, 4,950,229 (see column 8, lines 38-40); and 5,037,381.
- US Pat. No. 4,865,582 discloses an electrically powered transdermal drug applicator having a reusable power supply and a disposable drug reservoir.
- the drug reservoir has an adherent surface 13 which presumably has a release liner (similar to liner 48) affixed thereto prior to device assembly.
- the end user peels off the release liner, then applies the adherent surface of the disposable drug reservoir to the reusable power supply/controller 54.
- the release liner is intended to mask or protect the adhesive prior to assembly of the device and is removed prior to alignment of the reusable and disposable components. Unfortunately it is sometimes difficult to precisely align the controller 54 with the disposable component during mating of the two components.
- an object of the present invention to provide an electrotransport device having reusable and disposable components adapted to be adhesively mated, the alignment of which can be easily adjusted after the components have been brought in contact with one another.
- a further object of this invention to provide for the mechanical and electrical connection of the reusable and disposable components of an electrotransport device prior to adhesive mating of the components to one another.
- Yet another object of this invention is to provide a method of preventing premature adhesion of two components of an electrotransport device during alignment of the components.
- the electrotransport device of this invention which achieves these objects comprises two components which must be aligned and mated to one another prior to initiation of agent delivery.
- One component is a reusable component, preferably containing a power source and associated control circuitry.
- the other component is a disposable component which preferably includes the beneficial agent to be delivered.
- the disposable and reusable components have surfaces adapted to mate with and adhere to one another in a plurality of mating orientations, at least one of which is the desired mating orientation. At least one of the components has a mating surface having adhesive properties.
- the disposable component has the adhesive mating surface.
- Means are provided for aligning the reusable and disposable components in the desired mating orientation.
- An adhesive release liner is disposed on the adhesive mating surface.
- the liner prevents the mating surfaces from adhering to one another during alignment of the components. Once the components are aligned in the desired mating orientation, the liner is interposed between the mating surfaces. The liner is readily manually removable from this interposed position in order to permit adhesive mating of the components in the desired mating orientation.
- one or more mechanical connectors are provided both for mechanically connecting the components. Most preferably, the mechanical connection also serves to electrically connect the components.
- FIGURE 1 is a perspective view of one embodiment of the electrotransport device after connection of the reusable and disposable components and prior to removal of the removable liner.
- FIGURE 2 is an exploded view of the device of FIG. 1.
- FIGURE 3 is a plan view of the removable liner of FIG. 1 in an unfolded position.
- FIGURE 4 is a plan view of another embodiment of the removable liner of this invention in an unfolded position.
- FIGURE 5 is a perspective view of the removable liner of FIG. 4 in a folded position.
- FIGURE 6 is an exploded perspective view of one embodiment of an electrotransport device of this invention wherein the reusable and disposable components have corresponding indentations permitting exposure of a grasping means on the removable liner.
- FIGURE 7 is a cross sectional view of one embodiment of a disposable section of the present invention.
- FIGURE 8A is a plan view of one component of a two-piece removable liner embodiment in the unfolded position.
- FIGURE 8B is a plan view of the FIG. 8A component in a folded position.
- FIGURE 9A is a plan view of a second component of a two-piece removable liner embodiment in the unfolded position.
- FIGURE 9B is a plan view of the FIG. 9A component in a folded position.
- FIGURE 10 is a plan view of the assembled two-piece removable liner assembly incorporating FIGS. 7B and 8B liners.
- FIGURE 11 is an exploded perspective view of one embodiment of the electrotransport device having the two-piece removable liner of FIG. 10.
- FIGS. 1 and 2 illustrate one embodiment of an electrotransport device 1 of this invention.
- Device 1 comprises a reusable component 2, a disposable component 4 and a removable liner 8 disposed therebetween.
- Reusable component 2 preferably contains the electric power source and related control circuitry, while disposable component 4 preferably contains donor and counter electrodes and reservoirs, as shown more clearly in FIG. 6.
- the mating surface of one of the components, preferably the disposable component is adhesive so that the two components can be releasably bonded together after removal of the liner, as described in detail below. Further, the adhesive surface allows liner 8 to be releasably affixed on the disposable component during shipment of the component and assembly of the device.
- Fig. 1 shows components 2 and 4 in their desired mating orientation.
- Device 1 is provided with a means for aligning the components 2 and 4 in the desired mating orientation.
- the means for aligning components 2 and 4 are, in device 1, snap connectors.
- other conventional forms of alignment means may be used in place of snap connectors 6.
- the device is assembled by connecting the reusable component 2 and disposable component 4, to which liner 8 is releasably engaged, by joining male snap connectors 6 on component 4 to female snap connectors (not shown) on the underside of component 2.
- Access means 7 are provided in liner 8 to permit: (a) the male snap connectors 6 to be snapped into their female counterparts with the liner 8 interposed between the components 2 and 4; and (b) the liner 8 to be removed without disturbing the snap connectors 6.
- the aligning means also provides an initial mechanical connection and an electrical connection of the components 2 and 4.
- Snap connections 6 provide at least the additional function of mechanically connecting components 2 and 4, and in cases where the snap connectors 6 are composed of an electrically conductive material (eg, metal or metal coated snap connectors), they provide both additional functions.
- the liner 8 comprises a sheet of material folded over on itself at fold axis 8c to provide a first sheet portion 8a releasably adhered to the adherent mating surface 11 of component 4 and a second sheet portion 8b adjacent to component 2.
- the sheet should have a relatively low coefficient of friction to permit it to slide easily when pulled in the direction of the arrow in FIG. 2 by means of grasping means 10 on one of the ends of liner 8 opposite fold axis 8c.
- Access means in this embodiment are essentially parallel slots in the liner 8 which traverse fold axis 8c and are aligned with snap connectors 6 so that liner 8 does not interfere with the operation of snap connectors 6.
- the sheet portion 8b having grasping means 10 does not contact the component having the adhesive mating surface (ie, surface 11). In this manner, sheet portion 8b slides along a non-adhesive mating surface, as opposed to encountering substantially greater resistance by sliding along an adhesive mating surface.
- orienting liner 8 such that grasping means 10 is not adjacent the adhesive surface 11 minimizes the force required to extract liner 8 after alignment and initial connection of the components 2 and 4. Such an orientation benefits the patient or assembler of the device by reducing the difficulty of assembly.
- Snap connectors 6 align and mechanically connect the components 2 and 4 of the device in their desired mating orientation alignment, as shown in FIG. 1.
- liner 8 is removed by pulling on grasping means 10 in the direction of the arrow. This causes first surface 8a to unroll or peel from the adhesive mating surface 11 of component 4 by means of a tensile force acting essentially normal to surface 11 at the fold axis 8c, both initially and as the fold traverses the surface 11 of component 4.
- the force required to remove liner 8 is significantly less than the shear force, acting parallel to the adhesive surface 11 , that would be required to overcome the bond connecting liner 8 to component 4 over their entire contacting surfaces if liner 8 was in the form of a single sheet and was pulled in the direction of the arrow.
- the slots 7 are located such that fold axis 8c in the liner 8 is not impeded, by interaction with snap connectors 6, from traversing easily across the surfaces of components 2 and 4 as the liner 8 is pulled in the direction of the arrow in FIG. 2.
- FIGS. 2-5 illustrate two preferred embodiments according to the present invention. Both FIGS. 3 and 4 depict a plan view of a removable liner in an extended position, while FIGS. 2 and 5 illustrate corresponding folded positions of the same two liners, respectively.
- FIGS. 2 and 3 show an embodiment wherein a removable liner 8 has two elongated slots 7 therethrough. These elongated slots 7 are provided for mechanical/electrical connectors 6 which extend from disposable component 4 to reusable component 2 when the electrotransport device is assembled (See FIG. 1 for assembly). This design permits the liner to be pulled past the joined snap connectors 6 after alignment of components 2 and 4 is achieved.
- FIGS. 4 and 5 depict another embodiment wherein a removable liner 38 has four circular holes 9 therethrough. Holes directly opposite each other, separated by the fold axis 5, have perforations 3 extending between them.
- perforations refer both (1) to a continuous cut through the liner and (2) to alternating cut and un-cut portions through the liner.
- the perforations 3 aid in preventing tearing of liner 38 during removal thereof from a position interposed between the aligned reusable and disposable components of the electrotransport device.
- An advantage of this embodiment, as with the elongated slot design of FIG. 2 and 3, is that the liner 38 may be easily pulled past the snap connectors 6 after alignment of components 2 and 4.
- the liner 8 may be removed in order to effectively mate components 2 and 4.
- the removable liner 8 is removed by manually grasping and pulling the portion of the liner extending beyond the edges of the disposable and reusable components, on the side opposite the liner perforations or cuts.
- This extended liner portion is herein termed a grasping means 10, as shown in FIG. 2.
- the grasping means 10 preferably extends an adequate distance beyond both components 2 and 4 such that grasping with the user's fingers may be comfortably achievable.
- the grasping means 10 extends from about 6 mm to about 76 mm beyond the peripheral edge of aligned components 2 and 4. More preferably, the tab 10 extends from about 10 mm to about 25 mm beyond component 2 and 4.
- the adhesive coating preferably only on disposable component 4 provides a further means of mechanically securing the components to one another.
- both the reusable component 2 has an indentation 42 and the disposable component 4 has an indentation 44 in their peripheral edge which aligns with the edge of liner 8 which is opposite the fold axis 8c.
- the indentations are located such that they are substantially aligned when the device is assembled. These indentations provide manual access to an exposed portion of the liner 8, ie, another form of a grasping means 10. This alignment of indentations enables the user to more readily grasp the liner for removal purposes.
- the electrotransport device may be designed such that only one of the components 2 or 4 has an indentation exposing a portion of liner 8. The salient feature of this embodiment is that the liner 8 have a sufficient portion exposed so as to allow grasping of the liner for removal purposes.
- FIGURE 7 is a cross sectional view of one embodiment of a disposable component 4.
- the snap connectors 6 are composed of an electrically conductive material, and hence connectors 6 serve not only as the means for aligning the disposable component 4 in the desired mating orientation but also serve to (i) initially (ie, just prior to mating) mechanically connect the disposable component 4 to the reusable component 2; and (ii) electrically connect the electrodes 12 and 14 and the reservoirs 16 and 18 to the source of electrical power (eg, one or more batteries) in the reusable component 2.
- Male portions of snap connectors 6 conduct current from the power source (not shown) to donor and counter electrodes 12 and 14, respectively.
- the donor and counter electrodes 12 and 14 are electrically connected to donor and counter reservoirs 16 and 18, respectively.
- the donor electrode 12 and donor reservoir 16 are insulated from the counter electrode 14 and counter reservoir 18 by insulation 20 disposed therebetween.
- the electrodes and reservoirs are further insulated from the surroundings by peripheral insulation 21.
- Rate controlling membranes 30 and 32 such as disclosed in US Patent No. 5,080,646, can optionally be used to control the flux of donor and counter agents from the reservoirs 16 and 18.
- Adhesive surface 26 is provided for releasably affixing the disposable component 4 to the reusable component 2 as shown in FIG. 2.
- Removable liner 8 of the present invention is positioned on adhesive surface 26, thereby covering substantially all of the adhesive surface 26.
- Peripheral adhesive coating 28 on the skin contacting side of component 4 provides means by which the disposable component may be affixed to a body surface.
- Suitable self-adhering materials include, without limitation, poly(styrenebutadiene) and poly(styrene-isoprene-styrene) block copolymers, and polyisobutylene copolymers.
- Other suitable self-adhering matrix materials are set forth in the art such as are described in US Patent Nos. 4,391 ,278, 4,474,570, and 4,702,732, all of which are incorporated herein by reference.
- a second release liner 15 is preferably positioned adjacent adhesive surface 28, in order to isolate the adhesive coating 28 during shipping and handling of disposable component 4.
- FIGURES 8-10 illustrate another embodiment of the present invention wherein two folded removable liners form a removable liner assembly 70.
- Unfolded liners 50 and 60 are shown in FIGS. 8A and 9A, respectively.
- liners 50 and 60 Prior to use, liners 50 and 60 are folded at a fold axes 54 and 64, respectively, as shown in FIGS. 8B and 9B.
- the folded liners are assembled into the removable liner assembly 70, as shown in FIG. 10, which is configured such that access openings 72 are formed through which the alignment means, and optionally mechanical and/or electrical connectors, on the disposable and/or reusable components may pass.
- Grasping means 52 and 62 are preferably positioned opposite each other in the assembled 2-piece removable liner 70, as shown in FIG. 10.
- FIGURE 11 is an exploded perspective view of an embodiment of the electrotransport device of this invention having the two-piece removable liner assembly of FIG. 10.
- the device is assembled by first aligning removable liners 50 and 60 such that access openings 72 provide sufficient space for passing the male portions of the snap connectors 6 on the disposable component 4 therethrough for affixation to mating aligning and connecting means (not shown) on the underside of reusable component 2.
- aligning and connecting means have established alignment and initial mechanical connection of the components, the two removable liners 50 and 60 may be extracted by pulling grasping means 52 in the direction of the upper arrow, and then pulling grasping means 62 in the direction of the lower arrow.
- disposable component 4 is provided an adhesive mating surface 11 and the removable liners 50 and 60 affixed thereto.
- a skin contact adhesive is preferably also provided on the skin contacting surface of disposable component 4, which adhesive is also preferably protected by a removable liner (not shown in FIG. 11).
- the removable liner is preferably coated on at least one surface with a release coating, which allows only weak adhesive forces between the liner and the adhesive coating.
- a release coating may be used, including without limitation, polymer coatings, waxes, and silicones.
- release coating compositions and methods of applying release coatings which are useful with pressure-sensitive adhesives are disclosed in Handbook of Pressure-Sensitive Adhesive Technology. D. Satas, pp. 370-403 (Van Nostrand Reinhold Co., 1982), which is hereby incorporated by reference.
- the liner is coated with fluorocarbon diacrylate or a polymeric organic silicon material, more commonly referred to as a silicone. Silicones are preferred because silicones are commonly used, relatively inexpensive, and stable in most applications.
- both surfaces of the removable liner or liners may be coated with a release coating, this is not a requirement of the present invention. However, if the removable liner(s) have a release coating on only one side, the liner(s) are preferably folded such that the release coating surface is facing outward, ie, towards the reusable and disposable components. If the liners are coated on only the outer surface, the preferred removal process of liner assembly 70 in FIG. 10 involves first the removal of liner 50 by pulling grasping means 52. Subsequently, tab 62 may be pulled in order to remove liner 60. This sequence of liner removal minimizes the potential for the sticking of the non-coated liner surfaces to the adhesive during the removal process.
- One method of measuring the adhesion between the liner and adhesive coating involves first cutting liner/adhesive sample strips about 2 cm wide, and at least 4 inches long. Then, the liner and adhesive are manually separated at one end of the sample. The separated edge of the liner is attached to a stationary jaw of a tensile testing apparatus, such as a model 1122 tensile tester, available from Instron Corp., Canton, MA. The separated edge of the adhesive is placed in an opposing movable jaw of the tensile testing apparatus. Force is applied to the movable jaw by moving the movable jaw at a nearly constant rate, eg, 1000 mm/min. in a direction opposite the stationary jaw.
- a tensile testing apparatus such as a model 1122 tensile tester, available from Instron Corp., Canton, MA.
- Force is applied to the movable jaw by moving the movable jaw at a nearly constant rate, eg, 1000 mm/min. in a direction opposite the stationary jaw
- the adhesion is typically measured as the force required to separate the liner from the adhesive and is recorded in terms of grams and normalized by dividing by sample width.
- the adhesion between the liner and the adhesive material may range from about 5 to about 100 g/cm of liner width. More preferably, the adhesion between liner and adhesive is about 5 to about 50 g/cm of liner width. The most preferred range of adhesion to liner is about 5 to about 10 g/cm of liner width.
- Adhesives suitable for affixing the reusable component 2 to the disposable component 4 of the present invention include, without limitation, pressure sensitive adhesives such as polyacrylates, polyvinyl ethers, silicones, natural rubber, styrene-butadiene copolymers, styrene-isoprene copolymers, butyl rubber blended with polyisobutylene, butadiene- acrylonitrile rubbers, polychloroprene latex, polyurethanes, poly(vinyl pyrrolidone)s, vinyl pyrrolidone copolymers, ethylene vinyl acetates, and mixtures thereof.
- pressure sensitive adhesives such as polyacrylates, polyvinyl ethers, silicones, natural rubber, styrene-butadiene copolymers, styrene-isoprene copolymers, butyl rubber blended with polyisobutylene, butadiene- acrylonitrile rubbers, polych
- a more complete discussion of pressure-sensitive adhesives appears in Handbook of Pressure-Sensitive Adhesive Technology. D. Satas (Van Nostrand Reinhold Company, 1982), which is inco ⁇ orated herein by reference. In addition to moderate adhesive strengths, biocompatibility is a desirable adhesive characteristic.
- a more preferred group of adhesives for securing the components of the electrotransport device to one another includes silicones, polyacrylates, and polyisobutylenes.
- the thickness of the adhesive coating which secures the reusable component to the disposable component depends on a multitude of factors, including adhesive composition, the compositions of the surfaces which the adhesive contacts, desired adhesion and whether both components have an adhesive coating. Generally, the adhesive coating thickness ranges from about 0.025 mm to about 0.1 mm. More preferably, the adhesive coating thickness is about 0.4 mm to about 0.65 mm.
- the removable liner of the present invention may be composed of a variety of materials.
- the liner does not adhere strongly to the adhesive surface of either the disposable component and/or reusable component.
- a strong adhesion between the liner and the adhesive will cause the patient or user to experience difficulty in manually removing the liner.
- some adhesion between the liner and either disposable component or reusable component is required to hold the liner in place during manufacture, packaging, shipping and during the initial alignment step of the device assembly process.
- Suitable liner materials include, without limitation, polyesters, polyethylenes, poly(vinyl chloride)s, polypropylenes, polystyrenes, polyacrylonitriles, paper, cloth or fabric, and the like and combinations thereof. Some polymer materials, such as polyethylenes, may benefit from addition of mesh or scrim to add strength. Polyesters are more preferable liner materials, while the most preferred polyester is poly(ethylene terephthalate). Poly(ethylene terephthalate) is available commercially from 3M Corporation, Minneapolis, Minnesota.
- the thickness of the liner should be minimized while maintaining sufficient strength to prevent tearing upon removal.
- the required liner thickness is dependent upon the strength of the liner material and the adhesive force between the liner and the adhesive on disposable component and/or reusable component.
- the liner thickness preferably ranges from about 0.01 mm to about 0.25 mm. More preferably, the liner thickness is from about 0.025 mm to about 0.1 mm. Most preferably, the liner thickness ranges from about 0.06 mm to about 0.09 mm.
- the shape and dimensions of the removable liner are a function of the shape and dimensions of the component, or larger of the components, which have an adhesive coating thereon which faces the other component.
- components 2 and 4 have the same general size and shape.
- the removable liner is preferably sized to generally conform to the shape and size of the disposable and reusable components, with the exception of the grasping means as discussed above. However, the removable liner may extend beyond the edges of the components without causing significant problems. While the removable liner is not required to conform exactly to the size and shape of the reusable and disposable components, preferably the liner covers substantially all the adhesive coating or coatings of the components in order to prevent any premature adhesion.
- the electrodes of the present invention are composed of an electrically conductive material such as a metal.
- the electrodes may be formed from metal foil, metal screen, metal deposited or painted on a suitable backing, calendaring, film evaporation, or by embedding a metal powder in a binder matrix.
- suitable metals include silver, zinc, silver chloride, aluminum, platinum, stainless steel, gold, and titanium.
- the anodic electrode may be composed of silver
- the cathodic electrode may be composed of silver chloride.
- the electrodes may be formed of a polymer matrix containing a conductive filler such as a metal powder, powdered graphite, carbon fibers, or other electrically conductive filler material.
- a conductive filler such as a metal powder, powdered graphite, carbon fibers, or other electrically conductive filler material.
- the polymer- based electrodes may be produced by mixing the conductive filler in a polymer matrix, preferably a hydrophobic polymer matrix in order to minimize interaction with any water present in the reservoirs.
- the reusable component contains both a power source and control circuitry.
- the controller may allow manual or automatic feedback adjustment of current fed to the electrodes.
- the invention contemplates those electrotransport systems wherein the reusable component contains a power source without a controlling component. In this system, the agent delivery would be initiated once the agent-transmitting surface of the assembled device was contacted with a body surface.
- the reusable component may contain only control circuitry, while the power source is located in the disposable component. An example of this would be an electrotransport system is powered by entirely by a galvanic couple, wherein power is generated by two dissimilar electrodes.
- the electrodes themselves may generate at least a portion of the electrical power used to deliver the beneficial agent.
- the donor electrode and counter electrode are integral portions of the power generating process.
- Such a galvanic couple powered system activates automatically when body tissue and/or fluids form a complete circuit with the system.
- galvanic couple systems potentially useful in the present invention. Standard electrochemical reactions and the respective reduction potentials are well known in the art. For instance, see the CRC Handbook of Chemistry and Physics, pp. D133-D138, 62 nd edition (1981-1982), which is incorporated herein by reference.
- the electrotransport devices of the present invention use a separate electrical power source, apart from the power generated by way of the electrodes forming a galvanic couple.
- a power source is typically a battery or plurality of batteries, connected in series or in parallel, and positioned electrically between the counter electrode and donor electrode, such that the donor electrode is connected to one pole of the power source and the counter electrode is connected to the opposite pole.
- one or more 3 volt button cell batteries such as PANASONIC*® model CR 2025, are suitable to power electrotransport devices.
- the reusable component may include electronic circuitry for controlling the operation of the electrotransport device.
- the power source may include circuitry designed to permit the patient to manually turn the system on and off, such as with an on-demand medication regime, or to turn the system on and off at some desired periodicity, for example, to match the natural or circadian patterns of the body.
- a relatively simple controller or microprocessor could control the current as a function of time or could generate complex current waveforms such as pulses or sinusoidal waves.
- the control circuitry may also include a biosensor and some type of feedback system which monitors biosignals, provides an assessment of therapy, and adjusts the drug delivery accordingly.
- a typical example is the monitoring of the blood sugar level for controlled administration of insulin.
- the donor reservoir and optional counter reservoir can be any material adapted to abso ⁇ and hold a sufficient quantity of liquid therein in order to permit transport of agent therethrough by iontophoresis.
- gauzes, pads or sponges composed of cotton or other abso ⁇ ent fabric, both natural and synthetic may be used.
- the matrices of the reservoirs are composed, at least in part, of hydrophilic polymer material. Hydrophilic polymer is typically preferred because water is the preferred ion transport medium, and hydrophilic polymers have a relatively high equilibrium water content.
- the matrices of the reservoirs are solid polymer matrices composed, at least in part, of insoluble hydrophilic polymer. Insoluble hydrophilic polymer matrices are sometimes preferred for structural reasons over soluble hydrophilic polymers. However, it should be noted that hydrophobic polymers having a microporous structure sufficient to enable ion transport may be utilized in the agent reservoirs.
- the matrices can be crosslinked with the agent components in place such as a silastic matrix, or the polymers can be prefabricated and so ⁇ ed with the components from solutions as is the case with cellulose, woven fiber pads and sponges.
- the agent reservoirs can alternately be a gel matrix structure, formed similarly to the polymeric matrix structure, wherein the gel is formed of a hydrophilic polymer which is swellable or soluble in water.
- Such polymers can be blended with the components in any ratio, but preferably represent from a few percent up to about 50 percent by weight of the reservoir.
- the polymers can be linear or cross-linked.
- Suitable hydrophilic polymers include copolyesters such as HYTREL (DuPont De Nemours & Co., Wilmington, DE), polyvinylpyrrolidones, poly vinyl alcohol, polyethylene oxides such as POLYOX (Union Carbide Co ⁇ .), CARBOPOL (BF Goodrich of Akron, OH), blends of polyoxyethylene or polyethylene glycols with polyacryiic acid such as POLYOX blended with CARBOPOL, polyacrylamide, KLUCEL, cross-linked dextran such as SEPHADEX (Pharmacia Fine Chemicals, AB, Uppsala, Sweden), WATER LOCK (Grain Processing Co ⁇ ., Muscatine, Iowa) which is a starch-graft-poly(sodium acrylate-co-acrylamide) polymer, cellulose derivatives such as hydroxyethyl cellulose, hydroxypropylmethylcellulose, low-substituted hydroxypropylcellulose, and cross-linked Na- carboxymethyl
- the matrices of the reservoirs 16 and 18 may contain a hydrophobic polymer for enhanced structural rigidity.
- the hydrophobic polymer is heat fusible, in order to improve the lamination of the reservoirs to adjacent components, such as the insulator or a rate controlling membrane.
- Suitable hydrophobic polymers for use in the reservoir matrices include, but are not limited to, polyisobutylenes, polyethylene, polypropylene, polyisoprenes and polyalkenes, rubbers, copolymers such as KRATON, polyvinylacetate, ethylene vinyl acetate copolymers, polyamides such as nylons, polyurethanes, polyvinylchloride, acrylic or methacrylic resins such as polymers of esters of acrylic or methacrylic acid with alcohols such as n-butanol, 1 -methyl pentanol, 2-methyl pentanol, 3-methyl pentanol, 2-ethyl butanol, isooctanol, n-decanol, alone or copolymerized with ethylenically unsaturated monomers such as acrylic acid, methacrylic acid, acrylamide, methacrylamide, N-alkoxymethyl acrylamides, N-alkoxymethyl methacrylamide
- the reservoir matrices may be a polymeric matrix structure formed by blending the desired agent, drug, electrolyte, or other component(s), with an inert polymer by such processes as melt blending, solvent casting, or extrusion.
- the donor reservoir contains a agent to be delivered
- the counter reservoir contains an electrolyte, eg, a water soluble biocompatible salt, such as sodium chloride.
- the reservoirs may also contain other conventional materials such as dyes, pigments, inert fillers, and the like.
- This invention has utility in connection with the delivery of agents within the broad class deliverable through body surfaces, including skin, mucosa, and nails.
- drug and “agent” are used interchangeably herein and are intended to have their broadest inte ⁇ retation as any substance which is delivered to a living organism to produce a desired, usually beneficial, effect, in general, this includes therapeutic agents in all of the major therapeutic areas including, but not limited to, anti-infectives such as antibiotics and antiviral agents, analgesics including fentanyl, sufentanil, bupreno ⁇ hine and analgesic combinations, anesthetics, anorexics, antiarthritics, antiasthmatic agents such as terbutaline, anticonvulsants, antidepressants, antidiabetic agents, antidiarrheals, antihistamines, anti-inflammatory agents, antimigraine preparations, antimotion sickness preparations such as scopolamine and ondansetron, antinauseants, antine
- the invention is also useful in the controlled delivery of peptides, polypeptides, proteins and other macromolecules.
- macromolecular substances typically have a molecular weight of at least about 300 daltons, s and more typically a molecular weight in the range of about 300 to 40,000 daltons.
- the present invention has particular utility in delivering drugs whose delivery rate is dependent upon the physical activity of a patient.
- drugs and the corresponding patient motion or activity include the following: delivery of theophylline or epinephrine for the treatment of apnea; delivery of an antitussive such as dextromethorphan for the treatment of coughing; delivery of an anticonvulsant for the treatment of an epileptic seizure; delivery of insulin based upon the level of patient activity (eg, lower insulin delivery rate for more vigorous levels of patient activity); delivery of antiparkinson agent in response to patient shaking; delivery of antispasmodics such as diazepam for treatment of muscle spasms; and delivery of an antiemetic such as scopolamine or meclizine, in response to motion, for the treatment of motion sickness.
Landscapes
- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Bioinformatics & Cheminformatics (AREA)
- Animal Behavior & Ethology (AREA)
- Biomedical Technology (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Life Sciences & Earth Sciences (AREA)
- Pharmacology & Pharmacy (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Electrotherapy Devices (AREA)
- Electrical Discharge Machining, Electrochemical Machining, And Combined Machining (AREA)
- Valve Device For Special Equipments (AREA)
- Refuse Collection And Transfer (AREA)
Abstract
Description
Claims
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/069,270 US5445609A (en) | 1993-05-28 | 1993-05-28 | Electrotransport agent delivery device having a disposable component and a removable liner |
US69270 | 1993-05-28 | ||
PCT/US1994/006070 WO1994027671A1 (en) | 1993-05-28 | 1994-05-27 | Electrotransport agent delivery device |
Publications (2)
Publication Number | Publication Date |
---|---|
EP0700309A1 true EP0700309A1 (en) | 1996-03-13 |
EP0700309B1 EP0700309B1 (en) | 1997-03-05 |
Family
ID=22087843
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP94919291A Expired - Lifetime EP0700309B1 (en) | 1993-05-28 | 1994-05-27 | Electrotransport agent delivery device |
Country Status (7)
Country | Link |
---|---|
US (1) | US5445609A (en) |
EP (1) | EP0700309B1 (en) |
JP (1) | JP3504269B2 (en) |
AT (1) | ATE149363T1 (en) |
AU (1) | AU7048494A (en) |
DE (1) | DE69401938T2 (en) |
WO (1) | WO1994027671A1 (en) |
Families Citing this family (86)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5749847A (en) * | 1988-01-21 | 1998-05-12 | Massachusetts Institute Of Technology | Delivery of nucleotides into organisms by electroporation |
FR2709670B1 (en) * | 1993-09-10 | 1995-10-20 | Asulab Sa | Device in three modules for transdermal administration of drugs by electrophoresis or iontophoresis. |
EP0744971A1 (en) * | 1994-02-15 | 1996-12-04 | Biosearch Italia S.p.A. | Central venous catheters loaded with antibiotics of the ramoplanin group preventing development of catheter related infections |
CH693606A5 (en) * | 1995-05-15 | 2003-11-14 | Alza Corp | Electrotransport device having reusable controller. |
US5983131A (en) * | 1995-08-11 | 1999-11-09 | Massachusetts Institute Of Technology | Apparatus and method for electroporation of tissue |
US8321013B2 (en) | 1996-01-08 | 2012-11-27 | Impulse Dynamics, N.V. | Electrical muscle controller and pacing with hemodynamic enhancement |
US9289618B1 (en) | 1996-01-08 | 2016-03-22 | Impulse Dynamics Nv | Electrical muscle controller |
JP4175662B2 (en) | 1996-01-08 | 2008-11-05 | インパルス ダイナミクス エヌ.ヴイ. | Electric muscle control device |
US7167748B2 (en) | 1996-01-08 | 2007-01-23 | Impulse Dynamics Nv | Electrical muscle controller |
US8825152B2 (en) | 1996-01-08 | 2014-09-02 | Impulse Dynamics, N.V. | Modulation of intracellular calcium concentration using non-excitatory electrical signals applied to the tissue |
US9713723B2 (en) | 1996-01-11 | 2017-07-25 | Impulse Dynamics Nv | Signal delivery through the right ventricular septum |
USD384745S (en) * | 1996-01-23 | 1997-10-07 | Alza Corporation | Electrotransport drug delivery system |
US5961483A (en) * | 1996-06-19 | 1999-10-05 | Sage; Burton H. | Iontophoretic delivery of cell adhesion inhibitors |
US5857993A (en) * | 1996-07-12 | 1999-01-12 | Empi, Inc. | Process of making an iontophoresis electrode |
US5941843A (en) * | 1996-07-12 | 1999-08-24 | Empi, Inc. | Iontophoresis electrode |
US5871461A (en) * | 1996-07-12 | 1999-02-16 | Empi, Inc. | Method of making an iontophoresis electrode |
US5911223A (en) * | 1996-08-09 | 1999-06-15 | Massachusetts Institute Of Technology | Introduction of modifying agents into skin by electroporation |
US7840264B1 (en) | 1996-08-19 | 2010-11-23 | Mr3 Medical, Llc | System and method for breaking reentry circuits by cooling cardiac tissue |
US7908003B1 (en) | 1996-08-19 | 2011-03-15 | Mr3 Medical Llc | System and method for treating ischemia by improving cardiac efficiency |
US5797867A (en) * | 1996-09-27 | 1998-08-25 | Becton Dickinson And Company | Iontophoretic drug delivery system, including method for activating same for attachment to patient |
US5738647A (en) * | 1996-09-27 | 1998-04-14 | Becton Dickinson And Company | User activated iontophoretic device and method for activating same |
US5947920A (en) * | 1997-03-20 | 1999-09-07 | Dermion, Inc. | Self-contained hydrating system and iontophoresis bioelectrode |
US6085115A (en) * | 1997-05-22 | 2000-07-04 | Massachusetts Institite Of Technology | Biopotential measurement including electroporation of tissue surface |
DE69739334D1 (en) | 1997-07-16 | 2009-05-07 | Metacure N V | Device for controlling a smooth muscle |
US6949081B1 (en) * | 1998-08-26 | 2005-09-27 | Non-Invasive Technology, Inc. | Sensing and interactive drug delivery |
US6597946B2 (en) | 1998-11-09 | 2003-07-22 | Transpharma Ltd. | Electronic card for transdermal drug delivery and analyte extraction |
US6148232A (en) | 1998-11-09 | 2000-11-14 | Elecsys Ltd. | Transdermal drug delivery and analyte extraction |
US6611706B2 (en) | 1998-11-09 | 2003-08-26 | Transpharma Ltd. | Monopolar and bipolar current application for transdermal drug delivery and analyte extraction |
US6708060B1 (en) | 1998-11-09 | 2004-03-16 | Transpharma Ltd. | Handheld apparatus and method for transdermal drug delivery and analyte extraction |
US8700161B2 (en) | 1999-03-05 | 2014-04-15 | Metacure Limited | Blood glucose level control |
WO2006073671A1 (en) | 2004-12-09 | 2006-07-13 | Impulse Dynamics Nv | Protein activity modification |
US8666495B2 (en) | 1999-03-05 | 2014-03-04 | Metacure Limited | Gastrointestinal methods and apparatus for use in treating disorders and controlling blood sugar |
US9101765B2 (en) | 1999-03-05 | 2015-08-11 | Metacure Limited | Non-immediate effects of therapy |
US7092753B2 (en) * | 1999-06-04 | 2006-08-15 | Impulse Dynamics Nv | Drug delivery device |
US7190997B1 (en) * | 1999-06-04 | 2007-03-13 | Impulse Dynamics Nv | Drug delivery device |
US7171263B2 (en) * | 1999-06-04 | 2007-01-30 | Impulse Dynamics Nv | Drug delivery device |
US7030097B1 (en) * | 1999-07-14 | 2006-04-18 | Cornell Research Foundation, Inc. | Controlled nucleic acid delivery systems |
AU2002353444A1 (en) * | 2001-11-07 | 2003-05-19 | Transpharma Medical Ltd. | Integrated transdermal drug delivery system |
AU2003265226A1 (en) | 2002-03-11 | 2003-12-19 | Altea Therapeutics Corporation | Transdermal drug delivery device, method and use |
US9918665B2 (en) | 2002-03-11 | 2018-03-20 | Nitto Denko Corporation | Transdermal porator and patch system and method for using same |
US8116860B2 (en) | 2002-03-11 | 2012-02-14 | Altea Therapeutics Corporation | Transdermal porator and patch system and method for using same |
AU2003226605A1 (en) * | 2002-04-19 | 2003-11-03 | Transpharma Medical Ltd. | Handheld transdermal drug delivery and analyte extraction |
IL152575A (en) * | 2002-10-31 | 2008-12-29 | Transpharma Medical Ltd | Transdermal delivery system for water insoluble drugs |
IL152574A (en) * | 2002-10-31 | 2009-09-22 | Transpharma Medical Ltd | Transdermal delivery system for dried particulate or lyophilized medications |
US7383084B2 (en) * | 2002-10-31 | 2008-06-03 | Transpharma Medical Ltd. | Transdermal delivery system for dried particulate or lyophilized medications |
US7662404B2 (en) * | 2002-10-31 | 2010-02-16 | Transpharma Medical Ltd. | Transdermal delivery system for dried particulate or lyophilized peptides and polypeptides |
IL152573A (en) * | 2002-10-31 | 2009-11-18 | Transpharma Medical Ltd | Transdermal delivery system for anti-emetic medication |
US8133505B2 (en) * | 2002-10-31 | 2012-03-13 | Transpharma Medical Ltd. | Transdermal delivery system for dried particulate or lyophilized medications |
US6745071B1 (en) * | 2003-02-21 | 2004-06-01 | Birch Point Medical, Inc. | Iontophoretic drug delivery system |
US11439815B2 (en) | 2003-03-10 | 2022-09-13 | Impulse Dynamics Nv | Protein activity modification |
JP2006519663A (en) | 2003-03-10 | 2006-08-31 | インパルス ダイナミックス エヌヴイ | Apparatus and method for delivering electrical signals for regulating gene expression in heart tissue |
US8792985B2 (en) | 2003-07-21 | 2014-07-29 | Metacure Limited | Gastrointestinal methods and apparatus for use in treating disorders and controlling blood sugar |
US8016811B2 (en) | 2003-10-24 | 2011-09-13 | Altea Therapeutics Corporation | Method for transdermal delivery of permeant substances |
US11779768B2 (en) | 2004-03-10 | 2023-10-10 | Impulse Dynamics Nv | Protein activity modification |
US8352031B2 (en) | 2004-03-10 | 2013-01-08 | Impulse Dynamics Nv | Protein activity modification |
WO2005123173A1 (en) * | 2004-06-10 | 2005-12-29 | 3M Innovative Properties Company | Patch application device and kit |
US8252321B2 (en) | 2004-09-13 | 2012-08-28 | Chrono Therapeutics, Inc. | Biosynchronous transdermal drug delivery for longevity, anti-aging, fatigue management, obesity, weight loss, weight management, delivery of nutraceuticals, and the treatment of hyperglycemia, alzheimer's disease, sleep disorders, parkinson's disease, aids, epilepsy, attention deficit disorder, nicotine addiction, cancer, headache and pain control, asthma, angina, hypertension, depression, cold, flu and the like |
EP1802258A4 (en) | 2004-09-13 | 2015-09-23 | Chrono Therapeutics Inc | Biosynchronous transdermal drug delivery |
WO2006097934A2 (en) | 2005-03-18 | 2006-09-21 | Metacure Limited | Pancreas lead |
EP1898991B1 (en) | 2005-05-04 | 2016-06-29 | Impulse Dynamics NV | Protein activity modification |
US20080274166A1 (en) * | 2005-06-10 | 2008-11-06 | Transpharma Medical Ltd. | Patch for Transdermal Drug Delivery |
US20100016703A1 (en) * | 2006-07-13 | 2010-01-21 | Cardiac Bio-Systems Inc. | Bio-electrode possessing a hydrophilic skin-contacting layer and an electrolyte substance |
WO2008091878A1 (en) * | 2007-01-22 | 2008-07-31 | Altea Therapeutics Corporation | Transdermal porator and patch system and method for using same |
US20080234627A1 (en) * | 2007-03-22 | 2008-09-25 | Wanda Dent | Pivotally engaged multiple part electrotransport drug delivery device |
US8197844B2 (en) | 2007-06-08 | 2012-06-12 | Activatek, Inc. | Active electrode for transdermal medicament administration |
EP2644228A1 (en) | 2007-06-27 | 2013-10-02 | The General Hospital Corporation | Method and apparatus for optical inhibition of photodynamic therapy |
US20090043244A1 (en) * | 2007-08-08 | 2009-02-12 | Inan Omer T | Electrotransport Drug Delivery Device Adaptable to Skin Resistance Change |
WO2009047774A2 (en) * | 2007-10-09 | 2009-04-16 | Transpharma Ltd. | Magnetic patch coupling |
CA2696227A1 (en) * | 2007-10-17 | 2009-04-23 | Transpharma Medical Ltd. | Dissolution rate verification |
WO2009057112A2 (en) * | 2007-10-29 | 2009-05-07 | Transpharma Medical, Ltd. | Vertical patch drying |
KR101287351B1 (en) | 2007-12-05 | 2013-07-23 | 시네론 메디컬 리미티드 | A carrier for use in a skin treatment apparatus |
US8862223B2 (en) | 2008-01-18 | 2014-10-14 | Activatek, Inc. | Active transdermal medicament patch and circuit board for same |
US20090312689A1 (en) * | 2008-06-05 | 2009-12-17 | Alza Corporation | Adjustable Current Electrotransport Fentanyl Delivery Device |
US8606366B2 (en) | 2009-02-18 | 2013-12-10 | Syneron Medical Ltd. | Skin treatment apparatus for personal use and method for using same |
US8934975B2 (en) | 2010-02-01 | 2015-01-13 | Metacure Limited | Gastrointestinal electrical therapy |
CA2817824A1 (en) | 2010-11-23 | 2012-05-31 | Nupathe, Inc. | User-activated self-contained co-packaged iontophoretic drug delivery system |
US8301238B2 (en) | 2011-03-31 | 2012-10-30 | Incline Therapeutics, Inc. | Two-part electrotransport device |
US8428708B1 (en) | 2012-05-21 | 2013-04-23 | Incline Therapeutics, Inc. | Self-test for analgesic product |
US8428709B1 (en) | 2012-06-11 | 2013-04-23 | Incline Therapeutics, Inc. | Current control for electrotransport drug delivery |
CA2841785A1 (en) | 2011-07-06 | 2013-01-10 | The Parkinson's Institute | Compositions and methods for treatment of symptoms in parkinson's disease patients |
US10105487B2 (en) | 2013-01-24 | 2018-10-23 | Chrono Therapeutics Inc. | Optimized bio-synchronous bioactive agent delivery system |
AU2016211330A1 (en) | 2015-01-28 | 2017-08-03 | Chrono Therapeutics Inc. | Drug delivery methods and systems |
US10679516B2 (en) | 2015-03-12 | 2020-06-09 | Morningside Venture Investments Limited | Craving input and support system |
WO2018129304A1 (en) | 2017-01-06 | 2018-07-12 | Chrono Therapeutics Inc. | Transdermal drug delivery devices and methods |
EP3787505A4 (en) | 2018-05-04 | 2022-03-16 | Dexcom, Inc. | Systems and methods relating to an analyte sensor system having a battery located within a disposable base |
EP3801732A4 (en) | 2018-05-29 | 2022-04-27 | Morningside Venture Investments Limited | Drug delivery methods and systems |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4622031A (en) * | 1983-08-18 | 1986-11-11 | Drug Delivery Systems Inc. | Indicator for electrophoretic transcutaneous drug delivery device |
US4883457A (en) * | 1983-08-18 | 1989-11-28 | Drug Delivery Systems Inc. | Disposable and/or replenishable transdermal drug applicators and methods of manufacturing same |
US5135479A (en) * | 1983-08-18 | 1992-08-04 | Drug Delivery Systems, Inc. | Programmable control and mounting system for transdermal drug applicator |
US4627429A (en) * | 1986-02-28 | 1986-12-09 | American Home Products Corporation | Storage-stable transdermal adhesive patch |
AU597890B2 (en) * | 1986-03-14 | 1990-06-14 | Drug Delivery Systems Inc. | Transdermal drug applicator and electrodes therefor |
US5250022A (en) * | 1990-09-25 | 1993-10-05 | Rutgers, The State University Of New Jersey | Iontotherapeutic devices, reservoir electrode devices therefore, process and unit dose |
US4725263A (en) * | 1986-07-31 | 1988-02-16 | Medtronic, Inc. | Programmable constant current source transdermal drug delivery system |
US4865582A (en) * | 1987-06-05 | 1989-09-12 | Drug Delivery Systems Inc. | Disposable transdermal drug applicators |
US4942883A (en) * | 1987-09-29 | 1990-07-24 | Newman Martin H | Drug delivery device |
IL86076A (en) * | 1988-04-14 | 1992-12-01 | Inventor S Funding Corp Ltd | Transdermal drug delivery device |
DE3903794A1 (en) * | 1989-02-09 | 1990-08-16 | Lohmann Therapie Syst Lts | THERAPEUTIC SYSTEM FOR THE TRANSDERMAL OR TRANSMUCOSAL ADMINISTRATION OF ACTIVE SUBSTANCES AND ITS USE |
US5320597A (en) * | 1991-02-08 | 1994-06-14 | Becton, Dickinson And Company | Device and method for renewing electrodes during iontophoresis |
WO1991015261A1 (en) * | 1990-03-30 | 1991-10-17 | Medtronic, Inc. | Activity controlled electrotransport drug delivery device |
US5037381A (en) * | 1990-07-27 | 1991-08-06 | Bock C Randolph | Electrically assisted transdermal transport device and method for renewing the device |
-
1993
- 1993-05-28 US US08/069,270 patent/US5445609A/en not_active Expired - Lifetime
-
1994
- 1994-05-27 WO PCT/US1994/006070 patent/WO1994027671A1/en active IP Right Grant
- 1994-05-27 AU AU70484/94A patent/AU7048494A/en not_active Abandoned
- 1994-05-27 DE DE69401938T patent/DE69401938T2/en not_active Expired - Lifetime
- 1994-05-27 JP JP50101695A patent/JP3504269B2/en not_active Expired - Fee Related
- 1994-05-27 AT AT94919291T patent/ATE149363T1/en not_active IP Right Cessation
- 1994-05-27 EP EP94919291A patent/EP0700309B1/en not_active Expired - Lifetime
Non-Patent Citations (1)
Title |
---|
See references of WO9427671A1 * |
Also Published As
Publication number | Publication date |
---|---|
JPH09500292A (en) | 1997-01-14 |
AU7048494A (en) | 1994-12-20 |
DE69401938D1 (en) | 1997-04-10 |
US5445609A (en) | 1995-08-29 |
WO1994027671A1 (en) | 1994-12-08 |
DE69401938T2 (en) | 1997-10-09 |
JP3504269B2 (en) | 2004-03-08 |
ATE149363T1 (en) | 1997-03-15 |
EP0700309B1 (en) | 1997-03-05 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0700309B1 (en) | Electrotransport agent delivery device | |
US6169920B1 (en) | Iontophoretic drug delivery apparatus | |
EP0522011B1 (en) | Iontophoretic delivery device | |
US5298017A (en) | Layered electrotransport drug delivery system | |
US5162043A (en) | Iontophoretic delivery device | |
CA2181742C (en) | Reduction of skin irritation during electrotransport delivery | |
US5919155A (en) | Electrotransport system having flexible connector means | |
EP0643599B1 (en) | Iontophoretic delivery device | |
US6163720A (en) | Layered rate controlling membranes for use in an electrotransport device | |
CA2090313A1 (en) | Iontophoretic delivery device and method of hydrating same | |
IE904437A1 (en) | Improved iontophoretic delivery method | |
EP1455893B1 (en) | Electrotransport device having an integrally molded reservoir housing | |
CA2042994C (en) | Iontophoretic delivery device | |
CA2205010C (en) | Electrotransport device having reusable controller power saver |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
17P | Request for examination filed |
Effective date: 19951218 |
|
AK | Designated contracting states |
Kind code of ref document: A1 Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU NL PT SE |
|
RIN1 | Information on inventor provided before grant (corrected) |
Inventor name: GRACE, MICHAEL, J. Inventor name: DICKSON, DALE, A. Inventor name: LATTIN, GARY, A. |
|
GRAG | Despatch of communication of intention to grant |
Free format text: ORIGINAL CODE: EPIDOS AGRA |
|
17Q | First examination report despatched |
Effective date: 19960613 |
|
GRAH | Despatch of communication of intention to grant a patent |
Free format text: ORIGINAL CODE: EPIDOS IGRA |
|
GRAH | Despatch of communication of intention to grant a patent |
Free format text: ORIGINAL CODE: EPIDOS IGRA |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): AT BE CH DE DK ES FR GB GR IE IT LI LU NL PT SE |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: NL Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 19970305 Ref country code: LI Effective date: 19970305 Ref country code: IT Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT;WARNING: LAPSES OF ITALIAN PATENTS WITH EFFECTIVE DATE BEFORE 2007 MAY HAVE OCCURRED AT ANY TIME BEFORE 2007. THE CORRECT EFFECTIVE DATE MAY BE DIFFERENT FROM THE ONE RECORDED. Effective date: 19970305 Ref country code: GR Free format text: LAPSE BECAUSE OF FAILURE TO SUBMIT A TRANSLATION OF THE DESCRIPTION OR TO PAY THE FEE WITHIN THE PRESCRIBED TIME-LIMIT Effective date: 19970305 Ref country code: ES Free format text: THE PATENT HAS BEEN ANNULLED BY A DECISION OF A NATIONAL AUTHORITY Effective date: 19970305 Ref country code: DK Effective date: 19970305 Ref country code: CH Effective date: 19970305 Ref country code: BE Effective date: 19970305 Ref country code: AT Effective date: 19970305 |
|
REF | Corresponds to: |
Ref document number: 149363 Country of ref document: AT Date of ref document: 19970315 Kind code of ref document: T |
|
REG | Reference to a national code |
Ref country code: CH Ref legal event code: EP |
|
REF | Corresponds to: |
Ref document number: 69401938 Country of ref document: DE Date of ref document: 19970410 |
|
ET | Fr: translation filed | ||
REG | Reference to a national code |
Ref country code: IE Ref legal event code: FG4D Free format text: 72447 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: LU Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 19970527 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: SE Effective date: 19970605 Ref country code: PT Effective date: 19970605 |
|
NLV1 | Nl: lapsed or annulled due to failure to fulfill the requirements of art. 29p and 29m of the patents act | ||
REG | Reference to a national code |
Ref country code: CH Ref legal event code: PL |
|
PLBE | No opposition filed within time limit |
Free format text: ORIGINAL CODE: 0009261 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT |
|
26N | No opposition filed | ||
REG | Reference to a national code |
Ref country code: GB Ref legal event code: IF02 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GB Payment date: 20100329 Year of fee payment: 17 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: IE Payment date: 20100514 Year of fee payment: 17 Ref country code: FR Payment date: 20100525 Year of fee payment: 17 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DE Payment date: 20100519 Year of fee payment: 17 |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R119 Ref document number: 69401938 Country of ref document: DE |
|
REG | Reference to a national code |
Ref country code: DE Ref legal event code: R119 Ref document number: 69401938 Country of ref document: DE |
|
GBPC | Gb: european patent ceased through non-payment of renewal fee |
Effective date: 20110527 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: ST Effective date: 20120131 |
|
REG | Reference to a national code |
Ref country code: IE Ref legal event code: MM4A |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: FR Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20110531 Ref country code: IE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20110527 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: GB Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20110527 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20111130 |